Baroreflex activation therapy with conditional shut off

ABSTRACT

An embodiment of a baroreflex stimulator comprises a pulse generator to provide a baroreflex stimulation signal through an electrode, and a modulator to modulate the baroreflex stimulation signal based on a circadian rhythm template.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a continuation-in-part application of U.S. application Ser. No. 12/749,939, filed Mar. 30, 2010, now U.S. Pat. No. 8,131,373, which is a divisional application of U.S. application Ser. No. 10/746,844, filed Dec. 24, 2003, published as US 2005/0149130 on Jul. 7, 2005, now U.S. Pat. No. 7,706,884, both of which are herein incorporated by reference in their entirety.

This application is a continuation-in-part application of U.S. application Ser. No. 11/000,249, filed Nov. 30, 2004, published as US 2006/0116737 on Jun. 1, 2006, now U.S. Pat. No. 8,126,559, which is herein incorporated by reference in its entirety.

This application is a continuation-in-part application of U.S. application Ser. No. 11/279,188, filed Apr. 10, 2006, published as US 2007/0239210 on Oct. 11, 2007, now U.S. Pat. No. 7,783,349, which is herein incorporated by reference in its entirety.

This application is a continuation-in-part application of U.S. application Ser. No. 11/459,481, filed Jul. 24, 2006, published as US 2008/0021504 on Jan. 24, 2008, now U.S. Pat. No. 7,873,413, which is herein incorporated by reference in its entirety.

This application is also related to U.S. application Ser. No. 10/864,070, filed Jun. 8, 2004, now U.S. Pat. No. 7,194,313, which was filed as a divisional of U.S. application Ser. No. 10/746,844, now U.S. Pat. No. 7,706,884, both of which are incorporated by reference in their entirety.

The following commonly assigned U.S. patent applications are related, are all filed on Dec. 24, 2003 and are all herein incorporated by reference in their entirety: “Baroreflex Stimulation System to Reduce Hypertension,” U.S. patent application Ser. No. 10/746,134, published as US 2005/0149128 on Jul. 7, 2005, now U.S. Pat. No. 7,643,875; “Sensing With Compensation for Neural Stimulator,” U.S. patent application Ser. No. 10/746,847, published as US 2005/0149133 on Jul. 7, 2005, abandoned; “Implantable Baroreflex Stimulator with Integrated Pressure Sensor,” U.S. patent application Ser. No. 10/745,921, published as US 2005/0149143 on Jul. 7, 2005, now U.S. Pat. No. 7,869,881; “Automatic Baroreflex Modulation Based on Cardiac Activity,” U.S. patent application Ser. No. 10/746,846, published as US 2005/0149132 on Jul. 7, 2005, abandoned; “Automatic Baroreflex Modulation Responsive to Adverse Event,” U.S. patent application Ser. No. 10/745,925, published as US 2005/0149127 on Jul. 7, 2005, now U.S. Pat. No. 7,509,166; “Baroreflex Modulation to Gradually Increase Blood Pressure,” U.S. patent application Ser. No. 10/746,845, published as US 2005/0149131 on Jul. 7, 2005, now U.S. Pat. No. 7,486,991; “Baroreflex Stimulation to Treat Acute Myocardial Infarction,” U.S. patent application Ser. No. 10/745,920, published as US 2005/0149126 on Jul. 7, 2005, now U.S. Pat. No. 7,460,906; “Baropacing and Cardiac Pacing to Control Output,” U.S. patent application Ser. No. 10/746,135, published as US 2005/0149129 on Jul. 7, 2005; “A Lead for Stimulating the Baroreflex in the Pulmonary Artery,” U.S. patent application Ser. No. 10/746,861, published as US 2005/0149156 on Jul. 7, 2005, now U.S. Pat. No. 8,024,050; and “A Stimulation Lead for Stimulating the Baroreceptors in the Pulmonary Artery,” U.S. patent application Ser. No. 10/746,852, published as 2005/0149155 on Jul. 7, 2005, now U.S. Pat. No. 8,126,560.

TECHNICAL FIELD

This application relates generally to implantable medical devices and, more particularly, to synchronizing baroreflex stimulation to circadian rhythm.

BACKGROUND

Implanting a chronic electrical stimulator, such as a cardiac stimulator, to deliver medical therapy(ies) is known. Examples of cardiac stimulators include implantable cardiac rhythm management (CRM) device such as pacemakers, implantable cardiac defibrillators (ICDs), and implantable devices capable of performing pacing and defibrillating functions.

CRM devices are implantable devices that provide electrical stimulation to selected chambers of the heart in order to treat disorders of cardiac rhythm. An implantable pacemaker, for example, is a CRM device that paces the heart with timed pacing pulses. If functioning properly, the pacemaker makes up for the heart's inability to pace itself at an appropriate rhythm in order to meet metabolic demand by enforcing a minimum heart rate. Some CRM devices synchronize pacing pulses delivered to different areas of the heart in order to coordinate the contractions. Coordinated contractions allow the heart to pump efficiently while providing sufficient cardiac output.

Heart failure refers to a clinical syndrome in which cardiac function causes a below normal cardiac output that can fall below a level adequate to meet the metabolic demand of peripheral tissues. Heart failure may present itself as congestive heart failure (CHF) due to the accompanying venous and pulmonary congestion. Heart failure can be due to a variety of etiologies such as ischemic heart disease.

Hypertension is a cause of heart disease and other related cardiac co-morbidities. Hypertension occurs when blood vessels constrict. As a result, the heart works harder to maintain flow at a higher blood pressure, which can contribute to heart failure. A large segment of the general population, as well as a large segment of patients implanted with pacemakers or defibrillators, suffer from hypertension. The long term mortality as well as the quality of life can be improved for this population if blood pressure and hypertension can be reduced. Many patients who suffer from hypertension do not respond to treatment, such as treatments related to lifestyle changes and hypertension drugs.

A pressoreceptive region or field is capable of sensing changes in pressure, such as changes in blood pressure. Pressoreceptor regions are referred to herein as baroreceptors, which generally include any sensors of pressure changes. For example, baroreceptors include afferent nerves and further include sensory nerve endings that are sensitive to the stretching of the wall that results from increased blood pressure from within, and function as the receptor of a central reflex mechanism that tends to reduce the pressure. Baroreflex functions as a negative feedback system, and relates to a reflex mechanism triggered by stimulation of a baroreceptor. Increased pressure stretches blood vessels, which in turn activates baroreceptors in the vessel walls. Activation of baroreceptors naturally occurs through internal pressure and stretching of the arterial wall, causing baroreflex inhibition of sympathetic nerve activity (SNA) and a reduction in systemic arterial pressure. An increase in baroreceptor activity induces a reduction of SNA, which reduces blood pressure by decreasing peripheral vascular resistance.

The general concept of stimulating afferent nerve trunks leading from baroreceptors is known. For example, direct electrical stimulation has been applied to the vagal nerve and carotid sinus. Research has indicated that electrical stimulation of the carotid sinus nerve can result in reduction of experimental hypertension, and that direct electrical stimulation to the pressoreceptive regions of the carotid sinus itself brings about reflex reduction in experimental hypertension.

Electrical systems have been proposed to treat hypertension in patients who do not otherwise respond to therapy involving lifestyle changes and hypertension drugs, and possibly to reduce drug dependency for other patients.

SUMMARY

Various aspects and embodiments of the present subject matter provide baroreflex stimulation that mimics the natural circadian rhythm by providing stimulation levels that rise and fall during the day. Such stimulation, for example, promotes sleep or rest during certain portions of the day and promotes activity during other portions of the day.

An aspect of the present subject matter relates to a baroreflex stimulator. An embodiment of the stimulator comprises a pulse generator to provide a baroreflex stimulation signal through an electrode, and a modulator to modulate the baroreflex stimulation signal based on a circadian rhythm template.

An aspect of the present subject matter relates to a baroreflex stimulator. An embodiment of the stimulator comprises a pulse generator to provide a baroreflex stimulation signal through an electrode, and means for modulating the baroreflex stimulation signal based on a circadian rhythm.

An aspect of the present subject matter relates to a method for operating an implantable medical device. In an embodiment, a baroreflex stimulation therapy is applied using a baroreflex stimulator in the implantable medical device. The baroreflex stimulation therapy is modulated based on a circadian rhythm template. In one method embodiment, a circadian rhythm template is accessed, a baroreflex stimulation level is set based on the circadian rhythm template. Baroreflex stimulation is applied at the baroreflex stimulation level to a baroreceptor site in a pulmonary artery.

This Summary is an overview of some of the teachings of the present application and not intended to be an exclusive or exhaustive treatment of the present subject matter. Further details about the present subject matter are found in the detailed description and appended claims. Other aspects will be apparent to persons skilled in the art upon reading and understanding the following detailed description and viewing the drawings that form a part thereof, each of which are not to be taken in a limiting sense. The scope of the present invention is defined by the appended claims and their equivalents.

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1A and 1B illustrate neural mechanisms for peripheral vascular control.

FIGS. 2A-2C illustrate a heart.

FIG. 3 illustrates baroreceptors and afferent nerves in the area of the carotid sinuses and aortic arch.

FIG. 4 illustrates baroreceptors in and around the pulmonary artery.

FIG. 5 illustrates baroreceptor fields in the aortic arch, the ligamentum arteriosum and the trunk of the pulmonary artery.

FIG. 6 illustrates a known relationship between respiration and blood pressure when the baroreflex is stimulated.

FIG. 7 illustrates a blood pressure response to carotid nerve stimulation in a hypertensive dog during 6 months of intermittent carotid nerve stimulation.

FIG. 8 illustrates a system including an implantable medical device (IMD) and a programmer, according to various embodiments of the present subject matter.

FIG. 9 illustrates an implantable medical device (IMD) such as shown in the system of FIG. 8, according to various embodiments of the present subject matter.

FIGS. 10A-10C illustrate a baroreceptor stimulation lead with an integrated pressure sensor (IPS), according to various embodiments of the present subject matter.

FIG. 11 illustrates an implantable medical device (IMD) such as shown in FIG. 8 having a neural stimulator (NS) component and cardiac rhythm management (CRM) component, according to various embodiments of the present subject matter.

FIG. 12 illustrates a system including a programmer, an implantable neural stimulator (NS) device and an implantable cardiac rhythm management (CRM) device, according to various embodiments of the present subject matter.

FIG. 13 illustrates an implantable neural stimulator (NS) device such as shown in the system of FIG. 12, according to various embodiments of the present subject matter.

FIG. 14 illustrates an implantable cardiac rhythm management (CRM) device such as shown in the system of FIG. 12, according to various embodiments of the present subject matter.

FIG. 15 illustrates a programmer such as illustrated in the systems of FIGS. 8 and 12 or other external device to communicate with the implantable medical device(s), according to various embodiments of the present subject matter.

FIGS. 16A-16D illustrate a system and methods to prevent interference between electrical stimulation from a neural stimulator (NS) device and sensing by a cardiac rhythm management (CRM) device, according to various embodiments of the present subject matter.

FIG. 17 illustrates a system to modulate baroreflex stimulation, according to various embodiments of the present subject matter.

FIGS. 18A-18C illustrate methods for modulating baroreceptor stimulation based on a cardiac activity parameter, according to various embodiments of the present subject matter.

FIGS. 19A-19B illustrate methods for modulating baroreceptor stimulation based on a respiration parameter, according to various embodiments of the present subject matter.

FIGS. 20A-20B illustrate methods for modulating baroreceptor stimulation based on detection of an adverse event, according to various embodiments of the present subject matter.

FIGS. 21A-21E illustrate circadian rhythm.

FIG. 22 illustrates a method for modulating baroreceptor stimulation based on circadian rhythm, according to various embodiments of the present subject matter.

FIGS. 23A-B illustrate methods for modulating baroreceptor stimulation based on a cardiac output parameter, according to various embodiments of the present subject matter.

FIG. 24 illustrates a method for modulating baroreceptor stimulation to reverse remodel stiffening, according to various embodiments of the present subject matter.

FIGS. 25A-25B illustrate a system and method to detect myocardial infarction and perform baropacing in response to the detected myocardial infarction, according to various embodiments of the present subject matter.

FIG. 26 is a block diagram illustrating an embodiment of a circuit of a neural stimulation system.

FIG. 27 illustrates an embodiment of a therapy titration module.

FIG. 28 illustrates an implantable medical device (IMD), according to various embodiments of the present subject matter.

FIG. 29 shows a system diagram of an embodiment of a microprocessor-based implantable device, according to various embodiments.

FIG. 30 is a block diagram illustrating an embodiment of an external system.

FIG. 31 illustrates a system embodiment in which an IMD is placed subcutaneously or submuscularly in a patient's chest with lead(s) positioned to stimulate a vagus nerve.

FIG. 32 illustrates a system embodiment that includes an implantable medical device (IMD) with satellite electrode(s) positioned to stimulate at least one neural target.

DETAILED DESCRIPTION

The following detailed description of the present subject matter refers to the accompanying drawings which show, by way of illustration, specific aspects and embodiments in which the present subject matter may be practiced. These embodiments are described in sufficient detail to enable those skilled in the art to practice the present subject matter. Other embodiments may be utilized and structural, logical, and electrical changes may be made without departing from the scope of the present subject matter. References to “an”, “one”, or “various” embodiments in this disclosure are not necessarily to the same embodiment, and such references contemplate more than one embodiment. The following detailed description is, therefore, not to be taken in a limiting sense, and the scope is defined only by the appended claims, along with the full scope of legal equivalents to which such claims are entitled.

Hypertension and Baroreflex Physiology

A brief discussion of hypertension and the physiology related to baroreceptors is provided to assist the reader with understanding this disclosure. This brief discussion introduces hypertension, the autonomic nervous system, and baroreflex.

Hypertension is a cause of heart disease and other related cardiac co-morbidities. Hypertension generally relates to high blood pressure, such as a transitory or sustained elevation of systemic arterial blood pressure to a level that is likely to induce cardiovascular damage or other adverse consequences. Hypertension has been arbitrarily defined as a systolic blood pressure above 140 mm Hg or a diastolic blood pressure above 90 mm Hg. Hypertension occurs when blood vessels constrict. As a result, the heart works harder to maintain flow at a higher blood pressure. Consequences of uncontrolled hypertension include, but are not limited to, retinal vascular disease and stroke, left ventricular hypertrophy and failure, myocardial infarction, dissecting aneurysm, and renovascular disease.

The automatic nervous system (ANS) regulates “involuntary” organs, while the contraction of voluntary (skeletal) muscles is controlled by somatic motor nerves. Examples of involuntary organs include respiratory and digestive organs, and also include blood vessels and the heart. Often, the ANS functions in an involuntary, reflexive manner to regulate glands, to regulate muscles in the skin, eye, stomach, intestines and bladder, and to regulate cardiac muscle and the muscle around blood vessels, for example.

The ANS includes, but is not limited to, the sympathetic nervous system and the parasympathetic nervous system. The sympathetic nervous system is affiliated with stress and the “fight or flight response” to emergencies. Among other effects, the “fight or flight response” increases blood pressure and heart rate to increase skeletal muscle blood flow, and decreases digestion to provide the energy for “fighting or fleeing.” The parasympathetic nervous system is affiliated with relaxation and the “rest and digest response” which, among other effects, decreases blood pressure and heart rate, and increases digestion to conserve energy. The ANS maintains normal internal function and works with the somatic nervous system.

The subject matter of this disclosure generally refers to the effects that the ANS has on the heart rate and blood pressure, including vasodilation and vasoconstriction. The heart rate and force is increased when the sympathetic nervous system is stimulated, and is decreased when the sympathetic nervous system is inhibited (the parasympathetic nervous system is stimulated). FIGS. 1A and 1B illustrate neural mechanisms for peripheral vascular control. FIG. 1A generally illustrates afferent nerves to vasomotor centers. An afferent nerve conveys impulses toward a nerve center. A vasomotor center relates to nerves that dilate and constrict blood vessels to control the size of the blood vessels. FIG. 1B generally illustrates efferent nerves from vasomotor centers. An efferent nerve conveys impulses away from a nerve center.

Stimulating the systematic and parasympathetic nervous systems can have effects other than heart rate and blood pressure. For example, stimulating the sympathetic nervous system dilates the pupil, reduces saliva and mucus production, relaxes the bronchial muscle, reduces the successive waves of involuntary contraction (peristalsis) of the stomach and the motility of the stomach, increases the conversion of glycogen to glucose by the liver, decreases urine secretion by the kidneys, and relaxes the wall and closes the sphincter of the bladder. Stimulating the parasympathetic nervous system (inhibiting the sympathetic nervous system) constricts the pupil, increases saliva and mucus production, contracts the bronchial muscle, increases secretions and motility in the stomach and large intestine, and increases digestion in the small intention, increases urine secretion, and contracts the wall and relaxes the sphincter of the bladder. The functions associated with the sympathetic and parasympathetic nervous systems are many and can be complexly integrated with each other. Thus, an indiscriminate stimulation of the sympathetic and/or parasympathetic nervous systems to achieve a desired response, such as vasodilation, in one physiological system may also result in an undesired response in other physiological systems.

Baroreflex is a reflex triggered by stimulation of a baroreceptor. A baroreceptor includes any sensor of pressure changes, such as sensory nerve endings in the wall of the auricles of the heart, cardiac fat pads, vena cava, aortic arch and carotid sinus, that is sensitive to stretching of the wall resulting from increased pressure from within, and that functions as the receptor of the central reflex mechanism that tends to reduce that pressure. Additionally, a baroreceptor includes afferent nerve trunks, such as the vagus, aortic and carotid nerves, leading from the sensory nerve endings. Stimulating baroreceptors inhibits sympathetic nerve activity (stimulates the parasympathetic nervous system) and reduces systemic arterial pressure by decreasing peripheral vascular resistance and cardiac contractility. Baroreceptors are naturally stimulated by internal pressure and the stretching of the arterial wall.

Some aspects of the present subject matter locally stimulate specific nerve endings in arterial walls rather than stimulate afferent nerve trunks in an effort to stimulate a desire response (e.g. reduced hypertension) while reducing the undesired effects of indiscriminate stimulation of the nervous system. For example, some embodiments stimulate baroreceptor sites in the pulmonary artery. Some embodiments of the present subject matter involve stimulating either baroreceptor sites or nerve endings in the aorta, the chambers of the heart, the fat pads of the heart, and some embodiments of the present subject matter involve stimulating an afferent nerve trunk, such as the vagus, carotid and aortic nerves. Some embodiments stimulate afferent nerve trunks using a cuff electrode, and some embodiments stimulate afferent nerve trunks using an intravascular lead positioned in a blood vessel proximate to the nerve, such that the electrical stimulation passes through the vessel wall to stimulate the afferent nerve trunk.

FIGS. 2A-2C illustrate a heart. As illustrated in FIG. 2A, the heart 201 includes a superior vena cava 202, an aortic arch 203, and a pulmonary artery 204, and is useful to provide a contextual relationship with the illustrations in FIGS. 3-5. As is discussed in more detail below, the pulmonary artery 204 includes baroreceptors. A lead is capable of being intravascularly inserted through a peripheral vein and through the tricuspid valve into the right ventricle of the heart (not expressly shown in the figure) similar to a cardiac pacemaker lead, and continue from the right ventricle through the pulmonary valve into the pulmonary artery. A portion of the pulmonary artery and aorta are proximate to each other. Various embodiments stimulate baroreceptors in the aorta using a lead intravascularly positioned in the pulmonary artery. Thus, according to various aspects of the present subject matter, the baroreflex is stimulated in or around the pulmonary artery by at least one electrode intravascularly inserted into the pulmonary artery. Alternatively, a wireless stimulating device, with or without pressure sensing capability, may be positioned via catheter into the pulmonary artery. Control of stimulation and/or energy for stimulation may be supplied by another implantable or external device via ultrasonic, electromagnetic or a combination thereof. Aspects of the present subject matter provide a relatively noninvasive surgical technique to implant a baroreceptor stimulator intravascularly into the pulmonary artery.

FIGS. 2B-2C illustrate the right side and left side of the heart, respectively, and further illustrate cardiac fat pads which have nerve endings that function as baroreceptor sites. FIG. 2B illustrates the right atrium 267, right ventricle 268, sinoatrial node 269, superior vena cava 202, inferior vena cava 270, aorta 271, right pulmonary veins 272, and right pulmonary artery 273. FIG. 2B also illustrates a cardiac fat pad 274 between the superior vena cava and aorta. Baroreceptor nerve endings in the cardiac fat pad 274 are stimulated in some embodiments using an electrode screwed into the fat pad, and are stimulated in some embodiments using an intravenously-fed lead proximately positioned to the fat pad in a vessel such as the right pulmonary artery or superior vena cava, for example. FIG. 2C illustrates the left atrium 275, left ventricle 276, right atrium 267, right ventricle 268, superior vena cava 202, inferior vena cava 270, aorta 271, right pulmonary veins 272, left pulmonary vein 277, right pulmonary artery 273, and coronary sinus 278. FIG. 2C also illustrates a cardiac fat pad 279 located proximate to the right cardiac veins and a cardiac fat pad 280 located proximate to the inferior vena cava and left atrium. Baroreceptor nerve endings in the fat pad 279 are stimulated in some embodiments using an electrode screwed into the fat pad 279, and are stimulated in some embodiments using an intravenously-fed lead proximately positioned to the fat pad in a vessel such as the right pulmonary artery 273 or right pulmonary vein 272, for example. Baroreceptors in the 280 are stimulated in some embodiments using an electrode screwed into the fat pad, and are stimulated in some embodiments using an intravenously-fed lead proximately positioned to the fat pad in a vessel such as the inferior vena cava 270 or coronary sinus or a lead in the left atrium 275, for example.

FIG. 3 illustrates baroreceptors in the area of the carotid sinuses 305, aortic arch 303 and pulmonary artery 304. The aortic arch 303 and pulmonary artery 304 were previously illustrated with respect to the heart in FIG. 2A. As illustrated in FIG. 3, the vagus nerve 306 extends and provides sensory nerve endings 307 that function as baroreceptors in the aortic arch 303, in the carotid sinus 305 and in the common carotid artery 310. The glossopharyngeal nerve 308 provides nerve endings 309 that function as baroreceptors in the carotid sinus 305. These nerve endings 307 and 309, for example, are sensitive to stretching of the wall resulting from increased pressure from within. Activation of these nerve endings reduce pressure. Although not illustrated in the figures, the fat pads and the atrial and ventricular chambers of the heart also include baroreceptors. Cuffs have been placed around afferent nerve trunks, such as the vagal nerve, leading from baroreceptors to vasomotor centers to stimulate the baroreflex. According to various embodiments of the present subject matter, afferent nerve trunks can be stimulated using a cuff or intravascularly-fed lead positioned in a blood vessel proximate to the afferent nerves.

FIG. 4 illustrates baroreceptors in and around a pulmonary artery 404. The superior vena cava 402 and the aortic arch 403 are also illustrated. As illustrated, the pulmonary artery 404 includes a number of baroreceptors 411, as generally indicated by the dark area. Furthermore, a cluster of closely spaced baroreceptors is situated near the attachment of the ligamentum arteriosum 412. FIG. 4 also illustrates the right ventricle 413 of the heart, and the pulmonary valve 414 separating the right ventricle 413 from the pulmonary artery 404. According to various embodiments of the present subject matter, a lead is inserted through a peripheral vein and threaded through the tricuspid valve into the right ventricle, and from the right ventricle 413 through the pulmonary valve 414 and into the pulmonary artery 404 to stimulate baroreceptors in and/or around the pulmonary artery. In various embodiments, for example, the lead is positioned to stimulate the cluster of baroreceptors near the ligamentum arteriosum 412. FIG. 5 illustrates baroreceptor fields 511 in the aortic arch 503, near the ligamentum arteriosum 512 and the trunk of the pulmonary artery 504. Some embodiments position the lead in the pulmonary artery to stimulate baroreceptor sites in the aorta and/or fat pads, such as are illustrated in FIGS. 2B-2C.

FIG. 6 illustrates a known relationship between respiration 615 and blood pressure 616 when the left aortic nerve is stimulated. When the nerve is stimulated at 617, the blood pressure 616 drops, and the respiration 615 becomes faster and deeper, as illustrated by the higher frequency and amplitude of the respiration waveform. The respiration and blood pressure appear to return to the pre-stimulated state in approximately one to two minutes after the stimulation is removed. Various embodiments of the present subject matter use this relationship between respiration and blood pressure by using respiration as a surrogate parameter for blood pressure.

FIG. 7 illustrates a known blood pressure response to carotid nerve stimulation in a hypertensive dog during 6 months of intermittent carotid nerve stimulation. The figure illustrates that the blood pressure of a stimulated dog 718 is significantly less than the blood pressure of a control dog 719 that also has high blood pressure. Thus, intermittent stimulation is capable of triggering the baroreflex to reduce high blood pressure.

Baroreflex Stimulator Systems

Various embodiments of the present subject matter relate to baroreflex stimulator systems. Such baroreflex stimulation systems are also referred to herein as neural stimulator (NS) devices or components. Examples of neural stimulators include anti-hypertension (AHT) devices or AHT components that are used to treat hypertension. Various embodiments of the present subject matter include stand-alone implantable baroreceptor stimulator systems, include implantable devices that have integrated NS and cardiac rhythm management (CRM) components, and include systems with at least one implantable NS device and an implantable CRM device capable of communicating with each other either wirelessly or through a wire lead connecting the implantable devices. Integrating NS and CRM functions that are either performed in the same or separate devices improves aspects of the NS therapy and cardiac therapy by allowing these therapies to work together intelligently.

FIG. 8 illustrates a system 820 including an implantable medical device (IMD) 821 and a programmer 822, according to various embodiments of the present subject matter. Various embodiments of the IMD 821 include neural stimulator functions only, and various embodiments include a combination of NS and CRM functions. Some embodiments of the neural stimulator provide AHT functions. The programmer 822 and the IMD 821 are capable of wirelessly communicating data and instructions. In various embodiments, for example, the programmer 822 and IMD 821 use telemetry coils to wirelessly communicate data and instructions. Thus, the programmer can be used to adjust the programmed therapy provided by the IMD 821, and the IMD can report device data (such as battery and lead resistance) and therapy data (such as sense and stimulation data) to the programmer using radio telemetry, for example. According to various embodiments, the IMD 821 stimulates baroreceptors to provide NS therapy such as AHT therapy. Various embodiments of the IMD 821 stimulate baroreceptors in the pulmonary artery using a lead fed through the right ventricle similar to a cardiac pacemaker lead, and further fed into the pulmonary artery. According to various embodiments, the IMD 821 includes a sensor to sense ANS activity. Such a sensor can be used to perform feedback in a closed loop control system. For example, various embodiments sense surrogate parameters, such as respiration and blood pressure, indicative of ANS activity. According to various embodiments, the IMD further includes cardiac stimulation capabilities, such as pacing and defibrillating capabilities in addition to the capabilities to stimulate baroreceptors and/or sense ANS activity.

FIG. 9 illustrates an implantable medical device (IMD) 921 such as the IMD 821 shown in the system 820 of FIG. 8, according to various embodiments of the present subject matter. The illustrated IMD 921 performs NS functions. Some embodiments of the illustrated IMD 921 performs an AHT function, and thus illustrates an implantable AHT device. The illustrated device 921 includes controller circuitry 923 and a memory 924. The controller circuitry 923 is capable of being implemented using hardware, software, and combinations of hardware and software. For example, according to various embodiments, the controller circuitry 923 includes a processor to perform instructions embedded in the memory 924 to perform functions associated with NS therapy such as AHT therapy. For example, the illustrated device 921 further includes a transceiver 925 and associated circuitry for use to communicate with a programmer or another external or internal device. Various embodiments have wireless communication capabilities. For example, some transceiver embodiments use a telemetry coil to wirelessly communicate with a programmer or another external or internal device.

The illustrated device 921 further includes baroreceptor stimulation circuitry 926. Various embodiments of the device 921 also includes sensor circuitry 927. One or more leads are able to be connected to the sensor circuitry 927 and baroreceptor stimulation circuitry 926. The baroreceptor stimulation circuitry 926 is used to apply electrical stimulation pulses to desired baroreceptors sites, such as baroreceptor sites in the pulmonary artery, through one or more stimulation electrodes. The sensor circuitry 927 is used to detect and process ANS nerve activity and/or surrogate parameters such as blood pressure, respiration and the like, to determine the ANS activity.

According to various embodiments, the stimulator circuitry 926 includes modules to set any one or any combination of two or more of the following pulse features: the amplitude 928 of the stimulation pulse, the frequency 929 of the stimulation pulse, the burst frequency 930 or duty cycle of the pulse, and the wave morphology 931 of the pulse. Examples of wave morphology include a square wave, triangle wave, sinusoidal wave, and waves with desired harmonic components to mimic white noise such as is indicative of naturally-occurring baroreflex stimulation.

FIGS. 10A-10C illustrate a baroreceptor stimulation lead with an integrated pressure sensor (IPS), according to various embodiments of the present subject matter. Although not drawn to scale, these illustrated leads 1032A, 1032B and 1032C include an IPS 1033 with a baroreceptor stimulator electrode 1034 to monitor changes in blood pressure, and thus the effect of the baroreceptor stimulation. These lead illustrations should not be read as limiting other aspects and embodiments of the present subject matter. In various embodiments, for example, micro-electrical mechanical systems (MEMS) technology is used to sense the blood pressure. Some sensor embodiments determine blood pressure based on a displacement of a membrane.

FIGS. 10A-10C illustrate an IPS on a lead. Some embodiments implant an IPS in an IMD or NS device. The stimulator and sensor functions can be integrated, even if the stimulator and sensors are located in separate leads or positions.

The lead 1032A illustrated in FIG. 10A includes a distally-positioned baroreceptor stimulator electrode 1034 and an IPS 1033. This lead, for example, is capable of being intravascularly introduced to stimulate a baroreceptor site, such as the baroreceptor sites in the pulmonary artery, aortic arch, ligamentum arteriosum, the coronary sinus, in the atrial and ventricular chambers, and/or in cardiac fat pads.

The lead 1032B illustrated in FIG. 10B includes a tip electrode 1035, a first ring electrode 1036, second ring electrode 1034, and an IPS 1033. This lead may be intravascularly inserted into or proximate to chambers of the heart and further positioned proximate to baroreceptor sites such that at least some of the electrodes 1035, 1036 and 1034 are capable of being used to pace or otherwise stimulate the heart, and at least some of the electrodes are capable of stimulating at least one baroreceptor site. The IPS 1033 is used to sense the blood pressure. In various embodiments, the IPS is used to sense the blood pressure in the vessel proximate to the baroreceptor site selected for stimulation.

The lead 1032C illustrated in FIG. 10C includes a distally-positioned baroreceptor stimulator electrode 1034, an IPS 1033 and a ring electrode 1036. This lead 1032C may, for example, be intravascularly inserted into the right atrium and ventricle, and then through the pulmonary valve into the pulmonary artery. Depending on programming in the device, the electrode 1036 can be used to pace and/or sense cardiac activity, such as that which may occur within the right ventricle, and the electrode 1034 and IPS 1033 are located near baroreceptors in or near the pulmonary artery to stimulate and sense, either directly or indirectly through surrogate parameters, baroreflex activity.

Thus, various embodiments of the present subject matter provide an implantable NS device that automatically modulates baroreceptor stimulation using an IPS. Integrating the pressure sensor into the lead provides localized feedback for the stimulation. This localized sensing improves feedback control. For example, the integrated sensor can be used to compensate for inertia of the baroreflex such that the target is not continuously overshot. According to various embodiments, the device monitors pressure parameters such as mean arterial pressure, systolic pressure, diastolic pressure and the like. As mean arterial pressure increases or remains above a programmable target pressure, for example, the device stimulates baroreceptors at an increased rate to reduce blood pressure and control hypertension. As mean arterial pressure decreases towards the target pressure, the device responds by reducing baroreceptor stimulation. In various embodiments, the algorithm takes into account the current metabolic state (cardiac demand) and adjusts neural stimulation accordingly. A NS device having an IPS is able to automatically modulate baroreceptor stimulation, which allows an implantable NS device to determine the level of hypertension in the patient and respond by delivering the appropriate level of therapy. However, it is noted that other sensors, including sensors that do not reside in an NS or neural stimulator device, can be used to provide close loop feedback control.

FIG. 11 illustrates an implantable medical device (IMD) 1121 such as shown at 821 in FIG. 8 having an anti-hypertension (AHT) component 1137 and cardiac rhythm management (CRM) component 1138, according to various embodiments of the present subject matter. The illustrated device 1121 includes a controller 1123 and a memory 1124. According to various embodiments, the controller 1123 includes hardware, software, or a combination of hardware and software to perform the baroreceptor stimulation and CRM functions. For example, the programmed therapy applications discussed in this disclosure are capable of being stored as computer-readable instructions embodied in memory and executed by a processor. According to various embodiments, the controller 1123 includes a processor to execute instructions embedded in memory to perform the baroreceptor stimulation and CRM functions. The illustrated device 1121 further includes a transceiver and associated circuitry for use to communicate with a programmer or another external or internal device. Various embodiments include a telemetry coil.

The CRM therapy section 1138 includes components, under the control of the controller, to stimulate a heart and/or sense cardiac signals using one or more electrodes. The CRM therapy section includes a pulse generator 1139 for use to provide an electrical signal through an electrode to stimulate a heart, and further includes sense circuitry 1140 to detect and process sensed cardiac signals. An interface 1141 is generally illustrated for use to communicate between the controller 1123 and the pulse generator 1139 and sense circuitry 1140. Three electrodes are illustrated as an example for use to provide CRM therapy. However, the present subject matter is not limited to a particular number of electrode sites. Each electrode may include its own pulse generator and sense circuitry. However, the present subject matter is not so limited. The pulse generating and sensing functions can be multiplexed to function with multiple electrodes.

The NS therapy section 1137 includes components, under the control of the controller, to stimulate a baroreceptor and/or sense ANS parameters associated with nerve activity or surrogates of ANS parameters such as blood pressure and respiration. Three interfaces 1142 are illustrated for use to provide ANS therapy. However, the present subject matter is not limited to a particular number interfaces, or to any particular stimulating or sensing functions. Pulse generators 1143 are used to provide electrical pulses to an electrode for use to stimulate a baroreceptor site. According to various embodiments, the pulse generator includes circuitry to set, and in some embodiments change, the amplitude of the stimulation pulse, the frequency of the stimulation pulse, the burst frequency of the pulse, and the morphology of the pulse such as a square wave, triangle wave, sinusoidal wave, and waves with desired harmonic components to mimic white noise or other signals. Sense circuits 1144 are used to detect and process signals from a sensor, such as a sensor of nerve activity, blood pressure, respiration, and the like. The interfaces 1142 are generally illustrated for use to communicate between the controller 1123 and the pulse generator 1143 and sense circuitry 1144. Each interface, for example, may be used to control a separate lead. Various embodiments of the NS therapy section only include a pulse generator to stimulate baroreceptors. For example, the NS therapy section provides AHT therapy.

An aspect of the present subject matter relates to a chronically-implanted stimulation system specially designed to treat hypertension by monitoring blood pressure and stimulating baroreceptors to activate the baroreceptor reflex and inhibit sympathetic discharge from the vasomotor center. Baroreceptors are located in various anatomical locations such as the carotid sinus and the aortic arch. Other baroreceptor locations include the pulmonary artery, including the ligamentum arteriosum, and sites in the atrial and ventricular chambers. In various embodiments, the system is integrated into a pacemaker/defibrillator or other electrical stimulator system. Components of the system include a high-frequency pulse generator, sensors to monitor blood pressure or other pertinent physiological parameters, leads to apply electrical stimulation to baroreceptors, algorithms to determine the appropriate time to administer stimulation, and algorithms to manipulate data for display and patient management.

Various embodiments relate to a system that seeks to deliver electrically mediated NS therapy, such as AHT therapy, to patients. Various embodiments combine a “stand-alone” pulse generator with a minimally invasive, unipolar lead that directly stimulates baroreceptors in the vicinity of the heart, such as in the pulmonary artery. This embodiment is such that general medical practitioners lacking the skills of specialist can implant it. Various embodiments incorporate a simple implanted system that can sense parameters indicative of blood pressure. This system adjusts the therapeutic output (waveform amplitude, frequency, etc.) so as to maintain a desired quality of life. In various embodiments, an implanted system includes a pulse generating device and lead system, the stimulating electrode of which is positioned near endocardial baroreceptor tissues using transvenous implant technique(s). Another embodiment includes a system that combines NS therapy with traditional bradyarrhythmia, tachyarrhythmia, and/or congestive heart failure (CHF) therapies. Some embodiments use an additional “baroreceptor lead” that emerges from the device header and is paced from a modified traditional pulse generating system. In another embodiment, a traditional CRM lead is modified to incorporate proximal electrodes that are naturally positioned near baroreceptor sites. With these leads, distal electrodes provide CRM therapy and proximate electrodes stimulate baroreceptors.

A system according to these embodiments can be used to augment partially successful treatment strategies. As an example, undesired side effects may limit the use of some pharmaceutical agents. The combination of a system according to these embodiments with reduced drug doses may be particularly beneficial.

According to various embodiments, the lead(s) and the electrode(s) on the leads are physically arranged with respect to the heart in a fashion that enables the electrodes to properly transmit pulses and sense signals from the heart, and with respect to baroreceptors to stimulate the baroreflex. As there may be a number of leads and a number of electrodes per lead, the configuration can be programmed to use a particular electrode or electrodes. According to various embodiments, the baroreflex is stimulated by stimulating afferent nerve trunks.

FIG. 12 illustrates a system 1220 including a programmer 1222, an implantable neural stimulator (NS) device 1237 and an implantable cardiac rhythm management (CRM) device 1238, according to various embodiments of the present subject matter. Various aspects involve a method for communicating between an NS device 1237, such as an AHT device, and a CRM device 1238 or other cardiac stimulator. In various embodiments, this communication allows one of the devices 1237 or 1238 to deliver more appropriate therapy (i.e. more appropriate NS therapy or CRM therapy) based on data received from the other device. Some embodiments provide on-demand communications. In various embodiments, this communication allows each of the devices 1237 and 1238 to deliver more appropriate therapy (i.e. more appropriate NS therapy and CRM therapy) based on data received from the other device. The illustrated NS device 1237 and the CRM device 1238 are capable of wirelessly communicating with each other, and the programmer is capable of wirelessly communicating with at least one of the NS and the CRM devices 1237 and 1238. For example, various embodiments use telemetry coils to wirelessly communicate data and instructions to each other. In other embodiments, communication of data and/or energy is by ultrasonic means.

In some embodiments, the NS device 1237 stimulates the baroreflex to provide NS therapy, and senses ANS activity directly or using surrogate parameters, such as respiration and blood pressure, indicative of ANS activity. The CRM device 1238 includes cardiac stimulation capabilities, such as pacing and defibrillating capabilities. Rather than providing wireless communication between the NS and CRM devices 1237 and 1238, various embodiments provide a communication cable or wire, such as an intravenously-fed lead, for use to communicate between the NS device 1237 and the CRM device 1238.

FIG. 13 illustrates an implantable neural stimulator (NS) device 1337 such as shown at 1237 in the system of FIG. 12, according to various embodiments of the present subject matter. FIG. 14 illustrates an implantable cardiac rhythm management (CRM) device 1438 such as shown at 1238 in the system of FIG. 12, according to various embodiments of the present subject matter. Functions of the components for the NS device 1337 were previously discussed with respect to FIGS. 9 and 11 (the NS component 1137), and functions of the components for the CRM device 1238 were previously discussed with respect to FIG. 11 (the CRM component 1138). In the interest of brevity, these discussions with respect to the NS and CRM functions are not repeated here. Various embodiments of the NS and CRM devices include wireless transceivers 1325 and 1425, respectively, to wirelessly communicate with each other. Various embodiments of the NS and CRM devices include a telemetry coil or ultrasonic transducer to wirelessly communicate with each other.

According to various embodiments, for example, the NS device is equipped with a telemetry coil, allowing data to be exchanged between it and the CRM device, allowing the NS device to modify therapy based on electrophysiological parameters such as heart rate, minute ventilation, atrial activation, ventricular activation, and cardiac events. In addition, the CRM device modifies therapy based on data received from the NS device, such as mean arterial pressure, systolic and diastolic pressure, and baroreceptors stimulation rate.

Some NS device embodiments are able to be implanted in patients with existing CRM devices, such that the functionality of the NS device is enhanced by receiving physiological data that is acquired by the CRM device. The functionality of two or more implanted devices is enhanced by providing communication capabilities between or among the implanted devices. In various embodiments, the functionality is further enhanced by designing the devices to wirelessly communicate with each other.

FIG. 15 illustrates a programmer 1522, such as the programmer 822 and 1222 illustrated in the systems of FIGS. 8 and 12, or other external device to communicate with the implantable medical device(s) 1237 and/or 1238, according to various embodiments of the present subject matter. An example of another external device includes Personal Digital Assistants (PDAs) or personal laptop and desktop computers in an Advanced Patient Management (APM) system. The illustrated device 1522 includes controller circuitry 1545 and a memory 1546. The controller circuitry 1545 is capable of being implemented using hardware, software, and combinations of hardware and software. For example, according to various embodiments, the controller circuitry 1545 includes a processor to perform instructions embedded in the memory 1546 to perform a number of functions, including communicating data and/or programming instructions to the implantable devices. The illustrated device 1522 further includes a transceiver 1547 and associated circuitry for use to communicate with an implantable device. Various embodiments have wireless communication capabilities. For example, various embodiments of the transceiver 1547 and associated circuitry include a telemetry coil for use to wirelessly communicate with an implantable device. The illustrated device 1522 further includes a display 1548, input/output (I/O) devices 1549 such as a keyboard or mouse/pointer, and a communications interface 1550 for use to communicate with other devices, such as over a communication network.

Programmed Therapy Applications

NS and/or CRM functions of a system, whether implemented in two separate and distinct implantable devices or integrated as components into one implantable device, includes processes for performing NS and/or CRM therapy or portions of the therapy. In some embodiments, the NS therapy provides AHT therapy. These processes can be performed by a processor executing computer-readable instructions embedded in memory, for example. These therapies include a number of applications, which have various processes and functions, some of which are identified and discussed below. The processes and functions of these therapies are not necessarily mutually exclusive, as some embodiments of the present subject matter include combinations of two or more of the below-identified processes and functions.

Accounting for Neural Stimulation to Accurately Sense Signals

FIGS. 16A-16D illustrate a system and methods to prevent interference between electrical stimulation from an neural stimulator (NS) device and sensing by a cardiac rhythm management (CRM) device, according to various embodiments of the present subject matter. Neural stimulation is accounted for to improve the ability to sense signals, and thus reduce or eliminate false positives associated with detecting a cardiac event. The NS device includes an AHT device in some embodiments. For example, the NS device communicates with and prevents or otherwise compensates for baroreflex stimulation such that the CRM device does not unintentionally react to the baroreflex stimulation, according to some embodiments. Some embodiments automatically synchronize the baroreflex stimulation with an appropriate refraction in the heart. For example, some systems automatically synchronize stimulation of baroreceptors in or around the pulmonary artery with atrial activation. Thus, the functions of the CRM device are not adversely affected by detecting far-field noise generated by the baroreflex stimulation, even when the baroreflex stimulations are generated near the heart and the CRM sensors that detect the cardiac electrical activation.

FIG. 16A generally illustrates a system 1654 that includes NS functions 1651 (such as may be performed by a NS device or a NS component in an integrated NS/CRM device), CRM functions 1652 (such as may be performed by a CRM device or a CRM component in an integrated NS/CRM device) and capabilities to communicate 1653 between the NS and CRM functions. The illustrated communication is bidirectional wireless communication. However, the present subject matter also contemplates unidirectional communication, and further contemplates wired communication. Additionally, the present subject matter contemplates that the NS and CRM functions 1651 and 1652 can be integrated into a single implantable device such that the communication signal is sent and received in the device, or in separate implantable devices. Although baroreflex stimulation as part of neural stimulation is specifically discussed, this aspect of the present subject matter is also applicable to prevent, or account or other wise compensate for, unintentional interference detectable by a sensor and generated from other electrical stimulators.

FIG. 16B illustrates a process where CRM functions do not unintentionally react to baroreflex stimulation, according to various embodiments. FIG. 16B illustrates a process where the NS device or component 1651 sends an alert or otherwise informs the CRM device or component when baroreceptors are being electrically stimulated. In the illustrated embodiment, the NS device/component determines at 1655 if electrical stimulation, such as baroreflex stimulation, is to be applied. When electrical stimulation is to be applied, the NS device or component 1651 sends at 1656 an alert 1657 or otherwise informs the CRM device or component 1652 of the electrical stimulation. At 1658, the electrical stimulation is applied by the NS device/component. At 1659 CRM therapy, including sensing, is performed. At 1660, the CRM device/component determines whether an alert 1657 has been received from the NS device/component. If an alert has been received, an event detection algorithm is modified at 1661 to raise a detection threshold, provide a blackout or blanking window, or otherwise prevent the electrical stimulation in the NS device or component from being misinterpreted as an event by the CRM device/component.

FIG. 16C illustrates a process where CRM functions do not unintentionally react to baroreflex stimulation, according to various embodiments. The CRM device/component 1652 determines a refractory period for the heart at 1662. At 1663, if a refractory period is occurring or is expected to occur in a predictable amount of time, an enable 1664 corresponding to the refractory is provided to the NS device/component 1651. The AHT device/component 1651 determines if electrical stimulation is desired at 1665. When desired, the AHT device/component applies electrical stimulation during a refractory period at 1666, as controlled by the enable signal 1664. FIG. 16D illustrates a refractory period at 1667 in a heart and a baroreflex stimulation 1668, and further illustrates that baroreflex stimulation is applied during the refractory period.

A refractory period includes both absolute and relative refractory periods. Cardiac tissue is not capable of being stimulated during the absolute refractory period. The required stimulation threshold during an absolute refractory period is basically infinite. The relative refractory period occurs after the absolute refractory period. During the relative refractory period, as the cardiac tissue begins to repolarize, the stimulation threshold is initially very high and drops to a normal stimulation threshold by the end of the relative refractory period. Thus, according to various embodiments, a neural stimulator applies neural stimulation during either the absolute refractory period or during a portion of the relative refractory period corresponding a sufficiently high stimulation threshold to prevent the neural stimulation from capturing cardiac tissue.

Various embodiments of the present subject matter relate to a method of sensing atrial activation and confining pulmonary artery stimulation to the atrial refractory period, preventing unintentional stimulation of nearby atrial tissue. An implantable baroreceptor stimulation device monitors atrial activation with an atrial sensing lead. A lead in the pulmonary artery stimulates baroreceptors in the vessel wall. However, instead of stimulating these baroreceptors continuously, the stimulation of baroreceptors in the pulmonary artery occurs during the atrial refractory period to avoid capturing nearby atrial myocardium, maintaining the intrinsic atrial rate and activation. Various embodiments of the present subject matter combine an implantable device for stimulating baroreceptors in the wall of the pulmonary artery with the capability for atrial sensing. Various embodiments stimulate baroreceptors in the cardiac fat pads, in the heart chambers, and/or afferent nerves.

FIG. 17 illustrates a system 1769 to modulate baroreflex stimulation, according to various embodiments of the present subject matter. The illustrated system 1769 includes a baroreflex stimulator 1751, such as stimulator to stimulate baroreceptors in and around the pulmonary artery. The baroreflex stimulator can be included in a stand-alone NS device or as a NS component in an integrated NS/CRM device, for example. The illustrated stimulator 1751 includes a modulator 1769 for use to selectively increase and decrease the applied baroreflex stimulation. According to various embodiments, the modulator 1769 includes any one of the following modules: a module 1770 to change the amplitude of the stimulation pulse; a module 1771 to change the frequency of the stimulation pulse; and a module 1772 to change the burst frequency of the stimulation pulse. The burst frequency can also be referred to as a duty cycle. According to various embodiments, the modulator 1769 includes functions for the various combinations of two or more of the modules 1770, 1771 and 1772. Additionally, a stimulator can include a waveform generator capable of providing different waveforms in response to a control signal.

Various embodiments of the system include any one or any combination of a cardiac activity monitor 1773, an adverse event detector 1774, a respiration monitor 1775, and a circadian rhythm template 1776 which are capable of controlling the modulator 1769 of the stimulator 1759 to appropriately apply a desired level of baroreflex stimulation. Each of these 1773, 1774, 1775, and 1776 are associated with a method to modulate a baroreflex signal. According to various embodiments, the system includes means to modulate a baroreflex signal based on the following parameters or parameter combinations: cardiac activity (1773); an adverse event (1774); respiration (1775); circadian rhythm (1776); cardiac activity (1773) and an adverse event (1774); cardiac activity (1773) and respiration (1775); cardiac activity (1773) and circadian rhythm (1776); an adverse event (1774) and respiration (1775); an adverse event (1774) and circadian rhythm (1776); respiration (1775) and circadian rhythm (1776); cardiac activity (1773), an adverse event (1774), and respiration (1775); cardiac activity (1773), an adverse event (1774), and circadian rhythm (1776); cardiac activity (1773), respiration (1775), and circadian rhythm (1776); an adverse event (1774), respiration (1775) and circadian rhythm (1776); and cardiac activity (1773), an adverse event (1774), respiration (1775) and circadian rhythm (1776).

The stimulation can be applied to an afferent nerve trunk such as the vagal nerve using a cuff electrode or an intravascularly-fed lead positioned proximate to the nerve trunk. The stimulation can be applied to baroreceptor sites such are located in the pulmonary artery, aortic arch, and carotid sinus, for example, using intravenously-fed leads. The stimulation can be applied to baroreceptor sites located in cardiac fat pads using intravenously-fed leads or by screwing electrodes into the fat pads. Embodiments of the cardiac activity detector 1774, for example, include any one or any combination of a heart rate monitor 1777, a minute ventilation monitor 1778, and an acceleration monitor 1779. The respiration monitor 1775 functions as a surrogate for monitoring blood pressure. Embodiments of the respiration monitor 1775 include any one or any combination of a tidal volume monitor 1780 and a minute ventilation module 1781. Embodiments of the circadian rhythm template 1776 include any one or combination of a custom generated template 1782 and a preprogrammed template 1783. These embodiments are discussed in more detail below with respect to FIGS. 18A-18C, 19A-19B, 20A-20B, 21A-21E, 22 and 23A-23C.

Various embodiments use the circadian rhythm template to provide AHT therapy. Various embodiments use the circadian rhythm template to provide apnea therapy.

Modulation of Baroreflex Stimulation Based on Systolic Intervals

Activation of the sympathetic or parasympathetic nervous systems is known to alter certain systolic intervals, primarily the pre-ejection period (PEP), the time interval between sensed electrical activity within the ventricle (e.g. sensing of the “R” wave) and the onset of ventricular ejection of blood. The PEP may be measured from the sensed electrical event to the beginning of pressure increase in the pulmonary artery, using a pulmonary arterial pressure sensor, or may be measured to the beginning of an increase in intracardiac impedance, accompanying a decrease in ventricular volume during ejection, using electrodes positioned in the right or spanning the left ventricle. At rest, as determined by heart rate or body activity measured with an accelerometer for example, neural stimulation is modulated to maintain PEP in a pre-programmed range. A sudden decrease in PEP indicates an increase in sympathetic tone associated with exercise or emotional stress. This condition may be used to decrease neural stimulation permitting increases in heart rate and contractility necessary to meet metabolic demand. In like manner, a subsequent dramatic lengthening of PEP marks the end of increased metabolic demand. At this time control of blood pressure with neural stimulation could recommence.

Modulation of Baroreflex Stimulation Based on Cardiac Activity

The present subject matter describes a method of automatically modulating baroreceptor stimulation based on cardiac activity, such as can be determined by the heart rate, minute ventilation, acceleration and combinations thereof. The functionality of a device for electrically stimulating baroreceptors is enhanced by applying at least a relatively high baropacing rate during rest when metabolic demand is relatively low, and progressively less baropacing during physical exertion as metabolic demand increases. Indices of cardiac activity are used to automatically modulate the electrical stimulation of baroreceptors, allowing an implantable anti-hypertension device to respond to changes in metabolic demand. According to various embodiments, a CRM device, such as a pacemaker, AICD or CRT devices, also has a baroreceptor stimulation lead. The device monitors cardiac activity through existing methods using, for example, a blended sensor. A blended sensor includes two sensors to measure parameters such as acceleration and minute ventilation. The output of the blended sensor represents a composite parameter. Various NS and AHT therapies use composite parameters derived from two or more sensed parameters as discussed within this disclosure. At rest (lower cardiac activity) the device stimulates baroreceptors at a higher rate, reducing blood pressure and controlling hypertension. As cardiac activity increases, the device responds by temporarily reducing baroreceptor stimulation. This results in a temporary increase in blood pressure and cardiac output, allowing the body to respond to increased metabolic demand. For example, some embodiments provide baroreflex stimulation during rest and withdraw baroreflex stimulation during exercise to match normal blood pressure response to exercise. A pressure transducer can be used to determine activity. Furthermore, activity can be sensed using sensors that are or have been used to drive rate adaptive pacing. Examples of such sensors include sensor to detect body movement, heart rate, QT interval, respiration rate, transthoracic impedance, tidal volume, minute ventilation, body posture, electroencephalogram (EEG), electrocardiogram (ECG), electrooculogram (EOG), electromyogram (EMG), muscle tone, body temperature, pulse oximetry, time of day and pre-ejection interval from intracardiac impedance.

Various embodiments of the cardiac activity monitor includes a sensor to detect at least one pressure parameter such as a mean arterial parameter, a pulse pressure determined by the difference between the systolic and diastolic pressures, end systolic pressure (pressure at the end of the systole), and end diastolic pressure (pressure at the end of the diastole). Various embodiments of the cardiac activity monitor include a stroke volume monitor. Heart rate and pressure can be used to derive stroke volume. Various embodiments of the cardiac activity monitor use at least one electrogram measurement to determine cardiac activity. Examples of such electrogram measurements include the R-R interval, the P-R interval, and the QT interval. Various embodiments of the cardiac activity monitor use at least one electrocardiogram (ECG) measurement to determine cardiac activity.

FIGS. 18A-18C illustrate methods for modulating baroreceptor stimulation based on a cardiac activity parameter, according to various embodiments of the present subject matter. The cardiac activity can be determined by a CRM device, an NS device, or an implantable device with NS/CRM capabilities. A first process 1884A for modulating baroreceptor stimulation based on cardiac activity is illustrated in FIG. 18A. At 1885A the activity level is determined. According to various embodiments, the determination of activity level is based on heart rate, minute ventilation, acceleration or any combination of heart rate, minute ventilation, acceleration. In the illustrated process, the activity level has two defined binary levels (e.g. HI and LO). In some embodiments, the LO level includes no stimulation. It is determined whether the activity level is HI or LO. At 1886A, the baroreceptor stimulation level is set based on the determined activity level. A LO stimulation level is set if the activity level is determined to be HI, and a HI stimulation level is set if the activity level is determined to be LO.

A second process 1884B for modulating baroreceptor stimulation based on cardiac activity is illustrated in FIG. 18B. At 1885B the activity level is determined. According to various embodiments, the determination of activity level is based on heart rate, minute ventilation, acceleration or any combination of heart rate, minute ventilation, acceleration. In the illustrated process, the activity level has more than two defined levels or n defined levels. It is determined whether the activity level is level 1, level 2 . . . or level n. The activity level labels correspond to an increasing activity. At 1886B, the baroreceptor stimulation level is set based on the determined activity level. Available stimulation levels include level n . . . level 2 and level 1, where the stimulation level labels correspond to increasing stimulation. According to various embodiments, the selected baroreceptor stimulation level is inversely related to the determined activity level. For example, if it is determined that the cardiac activity level is at the highest level n, then the stimulation level is set to the lowest level n. If it determined that the stimulation level is at the first or second to the lowest level, level 1 or level 2 respectively, then the stimulation level is set to the first or second to the highest level, level 1 or level 2 respectively.

Another process 1884C for modulating baroreceptor stimulation based on cardiac activity is illustrated in FIG. 18C. At 1887, an acquired cardiac activity parameter is compared to a target activity parameter. If the acquired cardiac activity is lower than the target activity parameter, baroreceptor stimulation is increased at 1888. If the acquired cardiac activity is higher than the target activity parameter, baroreceptor stimulation is decreased at 1889.

An aspect of the present subject matter relates to a method of automatically modulating the intensity of baroreceptor stimulation based on respiration, as determined by tidal volume or minute ventilation. Instead of applying continuous baroreceptor stimulation, the NS device monitors the level of hypertension and delivers an appropriate level of therapy, using respiration as a surrogate for blood pressure, allowing the device to modulate the level of therapy. The present subject matter uses indices of respiration, such as impedance, to determined tidal volume and minute ventilation and to automatically modulate baroreceptor stimulation. Thus, an implantable NS device is capable of determining the level of hypertension in the patient and respond by delivering an appropriate level of therapy. In various embodiments, an implantable NS device contains a sensor to measure tidal volume or minute ventilation. For example, various embodiments measure transthoracic impedance to obtain a rate of respiration. The device receives this data from a CRM device in some embodiments. The NS device periodically monitors these respiration parameters. As respiration decreases or remains below a programmable target, the device stimulates baroreceptors at an increased rate, reducing blood pressure and controlling hypertension. As mean arterial pressure increases towards the target, the device responds by reducing baroreceptor stimulation. In this way, the AHT device continuously delivers an appropriate level of therapy.

FIGS. 19A-19B illustrate methods for modulating baroreceptor stimulation based on a respiration parameter, according to various embodiments of the present subject matter. The respiration parameter can be determined by a CRM device, an NS device, or an implantable device with NS/CRM capabilities. One embodiment of a method for modulating baroreceptor stimulation based on a respiration parameter is illustrated at 1910A in FIG. 19A. The respiration level is determined at 1911, and the baroreceptor stimulation level is set at 1912 based on the determined respiration level. According to various embodiments, the desired baropacing level is tuned at 1913. For example, one embodiment compares an acquired parameter to a target parameter at 1914. The baropacing can be increased at 1915 or decreased at 1916 based on the comparison of the acquired parameter to the target parameter.

One embodiment of a method for modulating baroreceptor stimulation based on a respiration parameter is illustrated at 1910B in FIG. 19B. At 1916, a baroreflex event trigger occurs, which triggers an algorithm for a baroreflex stimulation process. At 1917, respiration is compared to a target parameter. Baroreflex stimulation is increased at 1918 if respiration is below the target and is decreased at 1919 if respiration is above the target. According to various embodiments, the stimulation is not changed if the respiration falls within a blanking window. Various embodiments use memory to provide a hysteresis effect to stabilize the applied stimulation and the baroreflex response. Additionally, in various embodiments, the respiration target is modified during the therapy based on various factors such as the time of day or activity level. At 1920, it is determined whether to continue with the baroreflex therapy algorithm based on, for example, sensed parameters or the receipt of an event interrupt. If the baroreflex algorithm is to continue, then the process returns to 1917 where respiration is again compared to a target parameter; else the baroreflex algorithm is discontinued at 1921.

Modulation of Baroreflex Stimulation Based on Adverse Event

Aspects of the present subject matter include a method of automatically increasing baroreceptor stimulation upon detection of an adverse cardiac event to increase vasodilatory response and potentially prevent or reduce myocardial ischemic damage. Various embodiments include a feedback mechanism in a cardiac rhythm management device (such as a pacemaker, AICD or CRT device), which also has a stimulation lead for electrically stimulating baroreceptors. The device monitors cardiac electrical activity through existing methods. In the event of an adverse cardiac event such as ventricular fibrillation (VF) and atrial fibrillation (AF), ventricular tachycardia (VT) and atrial tachycardia (AT) above a predefined rate, and dyspnea as detected by a minute ventilation sensor, angina, decompensation and ischemia, the device responds by increasing baroreceptors stimulation to the maximally allowable level. As a result, blood pressure is temporarily lowered, potentially preventing or reducing myocardial damage due to ischemia. The functionality of a device to treat hypertension can be expanded if it can respond to adverse cardiac events by temporarily modulating the extent of baroreceptors stimulation. Event detection algorithms automatically modulate baroreceptors stimulation, allowing an implantable AHT device to respond to an adverse event by increasing baroreceptors stimulation, potentially preventing or reducing myocardial ischemic damage.

FIGS. 20A-20B illustrate methods for modulating baroreceptor stimulation based on detection of an adverse event, according to various embodiments of the present subject matter. The adverse event can be determined by a CRM device, an NS device, or an implantable device with NS/CRM capabilities. FIG. 20A illustrates one embodiment for modulating baroreceptor stimulation based on detection of an adverse event. At 2090A, it is determined whether an adverse event has been detected. If an adverse event has not been detected, normal baropacing (baropacing according to a normal routine) is performed at 2091A. If an adverse event has been detected, enhanced baropacing is performed at 2092. In various embodiments, the maximum allowable baropacing is performed when an adverse event is detected. Other baropacing procedures can be implemented. For example, various embodiments normally apply baropacing stimulation and withholds baropacing therapy when an adverse event is detected, and various embodiments normally withhold baropacing therapy and apply baropacing stimulation when an adverse event is detected. FIG. 20B illustrate on embodiment for modulating baroreceptor stimulation based on detection of an adverse event. At 2090B, it is determined whether an adverse event has been detected. If an adverse event has not been detected, normal baropacing (baropacing according to a normal routine) is performed at 2091B. If an adverse event has been detected, the event is identified at 2093, and the appropriate baropacing for the identified adverse event is applied at 2094. For example, proper blood pressure treatment may be different for ventricular fibrillation than for ischemia. According to various embodiments, the desired baropacing is tuned for the identified event at 2095. For example, one embodiment compares an acquired parameter to a target parameter at 2096. The baropacing can be increased at 2097 or decreased at 2098 based on the comparison of the acquired parameter to the target parameter.

According to various embodiments, an adverse event includes detectable precursors, such that therapy can be applied to prevent cardiac arrhythmia. In some embodiments, an adverse event includes both cardiac events and non-cardiac events such as a stroke. Furthermore, some embodiments identify both arrhythmic and non-arrhythmic events as adverse events.

Modulation of Baroreflex Stimulation Based on Circadian Rhythm

An aspect of the present subject matter relates to a method for stimulating the baroreflex in hypertension patients so as to mimic the natural fluctuation in blood pressure that occurs over a 24-hour period. Reflex reduction in hypertension is achieved during long-term baroreceptor stimulation without altering the intrinsic fluctuation in arterial pressure. According to various embodiments, an implantable device is designed to stimulate baroreceptors in the carotid sinus, pulmonary artery, or aortic arch using short, high-frequency bursts (such as a square wave with a frequency within a range from approximately 20-150 Hz), for example. Some embodiments directly stimulate the carotid sinus nerve, aortic nerve or vagus nerve with a cuff electrode. However, the bursts do not occur at a constant rate. Rather the stimulation frequency, amplitude, and/or burst frequency rises and falls during the day mimicking the natural circadian rhythm.

Thus, various embodiments of a NS device accounts for natural fluctuations in arterial pressure that occur in both normal and hypertensive individuals. Aside from activity-related changes in mean arterial pressure, subjects also exhibit a consistent fluctuation in pressure on a 24-hour cycle. A device which provides periodic baroreceptor stimulation mimics the intrinsic circadian rhythm, allowing for reflex inhibition of the systematic nervous system and reduced systemic blood pressure without disturbing this rhythm. The present subject matter provides a pacing protocol which varies the baroreceptor stimulation frequency/amplitude in order to reduce mean arterial pressure without disturbing the intrinsic circadian rhythm.

FIGS. 21A-21E illustrate circadian rhythm. FIG. 21A illustrates the circadian rhythm associated with mean arterial pressure for 24 hours from noon to noon; FIG. 21B illustrates the circadian rhythm associated with heart rate for 24 hours from noon to noon; FIG. 21C illustrates the circadian rhythm associated with percent change of stroke volume (SV %) for 24 hours from noon to noon; FIG. 21D illustrates the circadian rhythm associated with the percent change of cardiac output (CO) for 24 hours from noon to noon; and FIG. 21E illustrates the circadian rhythm associated with percent change of total peripheral resistance (TPR %), an index of vasodilation, for 24 hours from noon to noon. Various embodiments graph absolute values, and various embodiments graph percent values. In these figures, the shaded portion represents night hours from about 10 PM to 7 AM, and thus represents rest or sleep times. Referring to FIGS. 21A and 21B, for example, it is evident that both the mean arterial pressure and the heart rate are lowered during periods of rest. A higher blood pressure and heart rate can adversely affect rest. Additionally, a lower blood pressure and heart rate during the day can adversely affect a person's level of energy.

Various embodiments of the present subject matter modulate baroreflex stimulation using a pre-programmed template intended to match the circadian rhythm for a number of subjects. Various embodiments of the present subject matter generate a template customized to match a subject.

FIG. 22 illustrates a method for modulating baroreceptor stimulation based on circadian rhythm, according to various embodiments of the present subject matter, using a customized circadian rhythm template. The illustrated method 2222 senses and records parameters related to hypertension at 2223. Examples of such parameters include heart rate and mean arterial pressure. At 2224, a circadian rhythm template is generated based on these recorded parameters. At 2225, the baroreflex stimulation is modulated using the circadian rhythm template generated in 2224.

Modulation of Baroreflex Stimulation to Provide Desired Cardiac Output

An aspect of the present subject matter relates to an implantable medical device that provides NS therapy to lower systemic blood pressure by stimulating the baroreflex, and further provides cardiac pacing therapy using a cardiac pacing lead for rate control. Baroreflex stimulation and cardiac pacing occurs in tandem, allowing blood pressure to be lowered without sacrificing cardiac output.

According to various embodiments, a baroreflex stimulator communicates with a separate implantable CRM device, and uses the existing pacing lead. In various embodiments, baroreflex stimulation occurs through baroreceptors in the pulmonary artery, carotid sinus, or aortic arch with an electrode placed in or adjacent to the vessel wall. In various embodiments, afferent nerves such as the aortic nerve, carotid sinus nerve, or vagus nerve are stimulated directly with a cuff electrode.

Baroreflex stimulation quickly results in vasodilation, and decreases systemic blood pressure. To compensate for the concurrent decrease in cardiac output, the pacing rate is increased during baroreflex stimulation. The present subject matter allows blood pressure to be gradually lowered through baroreflex stimulation while avoiding the drop in cardiac output that otherwise accompanies such stimulation by combining baroreflex stimulation with cardiac pacing, allowing an implantable device to maintain cardiac output during blood pressure control.

FIG. 23A-B illustrate methods for modulating baroreceptor stimulation based on a cardiac output parameter, according to various embodiments of the present subject matter. FIG. 23A illustrates one embodiment for modulating baroreceptor stimulation based on a cardiac output parameter. In the illustrated process 2326A, it is determined whether baroreflex stimulation is being applied at 2327. If baroreflex stimulation is not being applied, the present subject matter implements the appropriate pacing therapy, if any, at 2328 with the appropriate pacing rate. If baroreflex stimulation is not being applied, the present subject matter implements a pacing therapy at 2329 with a higher pacing rate to maintain cardiac output.

FIG. 23B illustrates one embodiment for modulating baroreceptor stimulation based on a cardiac output parameter. In the illustrated process 2326B, baroreflex stimulation is applied at 2330, and it is determined whether the cardiac output is adequate at 2331. Upon determining that the cardiac output is not adequate, the pacing rate is increased at 2332 to maintain adequate cardiac output.

According to various embodiments, an existing pacing rate is increased by a predetermined factor during baroreflex stimulation to maintain cardiac output. In various embodiments, a pacing rate is initiated during baroreflex stimulation to maintain cardiac output. Modulating baroreflex stimulation to provide desired cardiac output can be implemented with atrial and ventricular rate control, AV delay control, resynchronization, and multisite stimulation. Alternatively, the stroke volume may be monitored by right ventricular impedance using electrodes within the right ventricular cavity or by left ventricular impedance using electrodes within or spanning the left ventricular cavity, and the pacing rate may be increased using application of neural stimulation to maintain a fixed cardiac output.

Modulation of Baroreflex Stimulation To Remodel Stiffening Process

Aspects of the present subject matter involve a method for baroreflex stimulation, used by an implantable NS device, to lower systemic blood pressure in patients with refractory hypertension. A baroreflex stimulation algorithm gradually increases baroreflex stimulation to slowly adjust blood pressure towards a programmable target. This algorithm prevents the central nervous system from adapting to a constant increased level of baroreflex stimulation, which ordinarily attenuates the pressure-lowering effect. In addition, the gradual nature of the blood pressure change allows the patient to better tolerate the therapy, without abrupt changes in systemic blood pressure and cardiac output.

The present subject matter provides a specific algorithm or process designed to prevent central nervous system adaptation to increased baroreflex stimulation, to slowly decrease blood pressure levels with time to enable for the reversion of the arterial stiffening process triggered by the previous hypertensive state present in the patient, and to prevent cardiac output decreases during baroreceptor stimulation. It is expected that, with time, the arterial system reverse remodels the stiffening process that was started by the previously present hypertension. The slow and progressive lowering of the mean/median blood pressure enables the slow reversion of this stiffening process through the reverse remodeling. Blood pressure is reduced without compromising cardiac output in the process, thus avoiding undesired patient symptoms.

In various embodiments, the device stimulates baroreceptors in the pulmonary artery, carotid sinus, or aortic arch with an electrode placed in or adjacent to the vessel wall. In various embodiments afferent nerves such as the aortic nerve, carotid sinus nerve, or vagus nerve are stimulated directly with a cuff electrode. The stimulated baroreflex quickly results in vasodilation, and a decrease in systemic blood pressure. However, rather than stimulating the baroreflex at a constant, elevated level, the device of the present subject matter initially stimulates at a slightly increased level, and then gradually increases the stimulation over a period of weeks or months, for example. The rate of change is determined by the device based on current and target arterial pressure. In various embodiments, the system determines the rate of change based on direct or indirect measurements of cardiac output, to ensure that the decrease in pressure is not occurring at the expense of a decreased cardiac output. In various embodiments, the rate of baroreflex stimulation is not constant but has a white noise type distribution to more closely mimic the nerve traffic distribution. By mimicking the nerve traffic distribution, it is expected that the baroreflex is more responsive to the stimulation, thus lowering the threshold for stimulating the baroreflex.

FIG. 24 illustrates a method for modulating baroreceptor stimulation to reverse remodel stiffening, according to various embodiments of the present subject matter. A baroreflex event trigger occurs at 2433. This trigger includes any event which initiates baroreflex stimulation, including the activation of an AHT device. At 2434, an algorithm is implemented to increase baroreflex stimulation by a predetermined rate of change to gradually lower the blood pressure to a target pressure in order to reverse remodel the stiffening process. At 2435, it is determined whether to continue with the baroreflex stimulation algorithm. The algorithm may be discontinued at 2436 based on an event interrupt, sensed parameters, and/or reaching the target blood pressure, for example. At 2437, it is determined whether the cardiac output is acceptable. If the cardiac output in not acceptable, at 2438 the rate of change for the baroreflex stimulate is modified based on the cardiac output.

Baroreflex Stimulation to Treat Myocardial Infarction

Following a myocardial infarction, myocytes in the infarcted region die and are replaced by scar tissue, which has different mechanical and elastic properties from functional myocardium. Over time, this infarcted area can thin and expand, causing a redistribution of myocardial stresses over the entire heart. Eventually, this process leads to impaired mechanical function in the highly stressed regions and heart failure. The highly stressed regions are referred to as being heavily “loaded” and a reduction in stress is termed “unloading.” A device to treat acute myocardial infarction to prevent or reduce myocardial damage is desirable.

An aspect of the present subject matter relates to an implantable device that monitors cardiac electrical activity. Upon detection of a myocardial infarction, the device electrically stimulates the baroreflex, by stimulating baroreceptors in or adjacent to the vessel walls and/or by directly stimulating pressure-sensitive nerves. Increased baroreflex stimulation compensates for reduced baroreflex sensitivity, and improves the clinical outcome in patients following a myocardial infarction. An implantable device (for example, a CRM device) monitors cardiac electrical activity. Upon detection of a myocardial infarction, the device stimulates the baroreflex. Some embodiments of the device stimulate baroreceptors in the pulmonary artery, carotid sinus, or aortic arch with an electrode placed in or adjacent to the vessel wall. In various embodiments, afferent nerves such as the aortic nerve are stimulated directly with a cuff electrode, or with a lead intravenously placed near the afferent nerve. Afferent nerves such as the carotid sinus nerve or vagus nerve are stimulated directly with a cuff electrode, or with a lead intravenously placed near the afferent nerve. In various embodiments, a cardiac fat pad is stimulated using an electrode screwed into the fat pad, or a lead intravenously fed into a vessel or chamber proximate to the fat pad.

Baroreflex stimulation quickly results in vasodilation, and a decrease in systemic blood pressure. This compensates for reduced baroreflex sensitivity and reduces myocardial infarction. According to various embodiments, systemic blood pressure, or a surrogate parameter, are monitored during baroreflex stimulation to insure that an appropriate level of stimulation is delivered. Some aspects and embodiments of the present subject matter provides baroreflex stimulation to prevent ischemic damage following myocardial infarction.

FIGS. 25A-25B illustrate a system and method to detect myocardial infarction and perform baropacing in response to the detected myocardial infarction, according to various embodiments of the present subject matter. FIG. 25A illustrates a system that includes a myocardial infarction detector 2539 and a baroreflex or baroreceptor stimulator 2540. A myocardial infarction can be detected using an electrocardiogram, for example. For example, a template can be compared to the electrocardiogram to determine a myocardial infarction. Another example detects changes in the ST segment elevation to detect myocardial infarction. In various embodiments, the detector 2539 and stimulator 2540 are integrated into a single implantable device such as in an AHT device or a CRM device, for example. In various embodiments, the detector 2539 and stimulator 2540 are implemented in separate implantable devices that are adapted to communicate with each other.

FIG. 25B illustrates a method to detect myocardial infarction and perform baropacing in response to the detected myocardial infarction, according to various embodiments of the present subject matter. At 2541, it is determined whether a myocardial infarction has occurred. Upon determining that a myocardial infarction has occurred, the baroreflex is stimulated at 2542. For example, in various embodiments, the baroreceptors in and around the pulmonary artery are stimulated using a lead fed through the right atrium and the pulmonary valve and into the pulmonary artery. Other embodiments stimulate other baroreceptor sites and pressure sensitive nerves. Some embodiments monitor the systemic blood pressure or a surrogate parameter at 2543, and determines at 2544 if the stimulation should be adjusted based on this monitoring. If the stimulation is to be adjusted, the baroreflex stimulation is modulated at 2545. Examples of modulation include changing the amplitude, frequency, burst frequency and/or waveform of the stimulation.

Neural stimulation, such as baroreflex stimulation, can be used to unload after a myocardial infarction. Various embodiments use an acute myocardial infarction detection sensor, such as an ischemia sensor, within a feedback control system of an NS device. However, a myocardial infarction detection sensor is not required. For example, a stimulation lead can be implanted after a myocardial infarction. In various embodiments, the stimulation lead is implanted through the right atrium and into the pulmonary artery to stimulate baroreceptors in and around the pulmonary artery. Various embodiments implant stimulation cuffs or leads to stimulate afferent nerves, electrode screws or leads to stimulate cardiac fat pads, and leads to stimulate other baroreceptors as provided elsewhere in this disclosure.

Electrical pre-excitation of a heavily loaded region will reduce loading on this region. This pre-excitation may significantly reduce cardiac output resulting in sympathetic activation and an increase in global stress, ultimately leading to deleterious remodeling of the heart. This process may be circumvented by increased neural stimulation to reduce the impact of this reflex. Thus, activation of the parasympathetic nervous system during pre-excitation may prevent the undesirable side-effects of unloading by electrical pre-excitation.

FIG. 26 is a block diagram illustrating an embodiment of a circuit of a neural stimulation system 2646. System 2646 includes a reference signal sensor 2647, a data sensor 2648 adapted to sense a physiologic response to the neural stimulation, a stimulation electrode/transducer 2649, and a neural stimulation circuit 2650. Reference signal sensor 2647 senses a reference signal indicative of cardiac cycles each including a predetermined type timing reference event. In one embodiment, reference signal sensor 2647 is an implantable reference signal sensor. The timing reference event is a recurring feature of the cardiac cycle that is chosen to be a timing reference to which the neural stimulation is synchronized. In an embodiment, reference signal sensor 2647 includes an electrode in or near the heart, such as may be incorporated in an intracardiac lead. In one embodiment, reference signal sensor 2647 is configured for extracardiac and extravascular placement, i.e., placement external to the heart and blood vessels. Examples of reference signal sensor 2647 include a set of electrodes for sensing a subcutaneous ECG signal, an acoustic sensor for sensing an acoustic signal indicative of heart sounds, and a hemodynamic sensor for sensing a hemodynamic signal indicative of hemodynamic performance. In one embodiment, an implantable medical device has an implantable housing that contains both a reference signal sensor 2647 and neural stimulation circuit 2650. In an embodiment, reference signal sensor 2647 is incorporated onto the housing of an implantable medical device. In another embodiment, reference signal sensor 2647 is electrically connected to an implantable medical device through one or more leads. In another embodiment, reference signal sensor 2647 is communicatively coupled to an implantable medical device via an intra-body telemetry link.

Neural stimulation circuit 2650 includes a stimulation output circuit 2651, a reference event detection circuit 2652, a feedback detection circuit 2653, and a stimulation control circuit 2654. Reference event detection circuit 2652 receives the reference signal from reference signal sensor 2647 and detects the timing reference event from the reference signal. Stimulation control circuit 2654 controls the delivery of the neural stimulation pulses and includes a synchronization circuit or module 2655 and a therapy titration adjustment circuit or module 2656. Synchronization module 2655 receives a signal indicative of the detection of each timing reference event and synchronizes the delivery of the neural stimulation pulses to the detected timing reference event. Stimulation output circuit 2651 delivers neural stimulation pulses upon receiving a pulse delivery signal from stimulation control circuit 2654. Data sensor 2648 provides signals indicative of a physiological response to the applied neural stimulation. A feedback detection circuit 2653 receives the signal indicative of the response and processes the signal to provide a neural stimulation feedback signal. In various embodiments, the response includes a cardiac activity such as heart rate, HRV, HRT, PR interval, T-wave velocity, or action potential duration. In various embodiments the response includes a non-cardiac response such as respiration or blood pressure. In various embodiments, the response includes a QT interval or atrial/ventricular refractory periods. The therapy titration/adjustment module 2656 uses the feedback signal to modulate or titrate the therapy generated by the stimulation output circuit 2651 to provide the desired physiologic response (e.g. cardiac response or non-cardiac response). Contextual sensor(s) or input(s) 2657 are also illustrated connected to the feedback detection circuit 2653 to provide a more complete picture of a patient's physiology. The feedback detection circuit can provide the neural stimulation feedback signal based on the sensor 2648 and the contextual input(s) 2657. The contextual input(s) can be used to avoid incomplete data from affecting the neural stimulation. Examples of contextual inputs include an activity sensor, a posture sensor and a timer. Any one or combination of two or more contextual inputs can be used by the feedback detection circuit. For example, an elevated heart rate may be representative of exercise rather than a reason for titrating the neural stimulation therapy.

FIG. 27 illustrates an embodiment of a therapy titration module 2756 such as is illustrated at 2656 in FIG. 26. According to various embodiments, the stimulation control circuit is adapted to set or adjust any one or any combination of stimulation features 2758. Examples of stimulation features include the amplitude, frequency, polarity and wave morphology of the stimulation signal. Examples of wave morphology include a square wave, triangle wave, sinusoidal wave, and waves with desired harmonic components to mimic white noise such as is indicative of naturally-occurring baroreflex stimulation. Some embodiments of the stimulation output circuit are adapted to generate a stimulation signal with a predetermined amplitude, morphology, pulse width and polarity, and are further adapted to respond to a control signal from the controller to modify at least one of the amplitude, wave morphology, pulse width and polarity. Some embodiments of the neural stimulation circuitry are adapted to generate a stimulation signal with a predetermined frequency, and are further adapted to respond to a control signal from the controller to modify the frequency of the stimulation signal.

The therapy titration module 2756 can be programmed to change stimulation sites 2759, such as changing the stimulation electrodes used for a neural target or changing the neural targets for the neural stimulation. For example, different electrodes of a multi-electrode cuff can be used to stimulate a neural target. Examples of neural targets include the right and left vagus nerves, cardiac branches of the vagus nerve, cardiac fats pads, baroreceptors, the carotid sinus, the carotid sinus nerve, and the aortic nerve. Autonomic neural targets can include afferent pathways and efferent pathways and can include sympathetic and parasympathetic nerves. The stimulation can include stimulation to stimulate neural traffic or stimulation to inhibit neural traffic. Thus, stimulation to evoke a sympathetic response can involve sympathetic stimulation and/or parasympathetic inhibition; and stimulation to evoke a parasympathetic response can involve parasympathetic stimulation and/or sympathetic inhibition.

The therapy titration module 2756 can be programmed to change stimulation vectors 2760. Vectors can include stimulation vectors between electrodes, or stimulation vectors for transducers. For example, the stimulation vector between two electrodes can be reversed. One potential application for reversing stimulation vectors includes changing from stimulating neural activity at the neural target to inhibiting neural activity at the neural target. More complicated combinations of electrodes can be used to provide more potential stimulation vectors between or among electrodes. One potential stimulation vector application involves selective neural stimulation (e.g. selective stimulation of the vagus nerve) or changing between a selective stimulation and a more general stimulation of a nerve trunk.

The therapy titration module 2756 can be programmed to control the neural stimulation according to stimulation instructions, such as a stimulation routine or schedule 2761, stored in memory. Neural stimulation can be delivered in a stimulation burst, which is a train of stimulation pulses at a predetermined frequency. Stimulation bursts can be characterized by burst durations and burst intervals. A burst duration is the length of time that a burst lasts. A burst interval can be identified by the time between the start of successive bursts. A programmed pattern of bursts can include any combination of burst durations and burst intervals. A simple burst pattern with one burst duration and burst interval can continue periodically for a programmed period or can follow a more complicated schedule. The programmed pattern of bursts can be more complicated, composed of multiple burst durations and burst interval sequences. The programmed pattern of bursts can be characterized by a duty cycle, which refers to a repeating cycle of neural stimulation ON for a fixed time and neural stimulation OFF for a fixed time. Duty cycle is specified by the ON time and the cycle time, and thus can have units of ON time/cycle time. According to some embodiments, the control circuit 2654 controls the neural stimulation generated by the stimulation circuitry by initiating each pulse of the stimulation signal. In some embodiments, the stimulation control circuit initiates a stimulation signal pulse train, where the stimulation signal responds to a command from the controller circuitry by generating a train of pulses at a predetermined frequency and burst duration. The predetermined frequency and burst duration of the pulse train can be programmable. The pattern of pulses in the pulse train can be a simple burst pattern with one burst duration and burst interval or can follow a more complicated burst pattern with multiple burst durations and burst intervals. In some embodiments, the stimulation control circuit controls the stimulation output circuit to initiate a neural stimulation session and to terminate the neural stimulation session. The burst duration of the neural stimulation session under the control of the control circuit 2654 can be programmable. The controller may also terminate a neural stimulation session in response to an interrupt signal, such as may be generated by one or more sensed parameters or any other condition where it is determined to be desirable to stop neural stimulation.

The illustrated device includes a programmed therapy schedule or routine stored in memory and further includes a clock or timer which can be used to execute the programmable stimulation schedule. For example, a physician can program a daily/weekly schedule of therapy based on the time of day. A stimulation session can begin at a first programmed time, and can end at a second programmed time. Various embodiments initiate and/or terminate a stimulation session based on a signal triggered by a user. Various embodiments use sensed data to enable and/or disable a stimulation session.

According to various embodiments, the stimulation schedule refers to the time intervals or period when the neural stimulation therapy is delivered. A schedule can be defined by a start time and an end time, or a start time and a duration. Various schedules deliver therapy periodically. By way of example and not limitation, a device can be programmed with a therapy schedule to deliver therapy from midnight to 2 AM every day, or to deliver therapy for one hour every six hours, or to deliver therapy for two hours per day, or according to a more complicated timetable. Various device embodiments apply the therapy according to the programmed schedule contingent on enabling conditions, such as sensed exercise periods, patient rest or sleep, low heart rate levels, and the like. For example, the stimulation can be synchronized to the cardiac cycle based on detected events that enable the stimulation. The therapy schedule can also specify how the stimulation is delivered.

FIG. 28 illustrates an implantable medical device (IMD), according to various embodiments of the present subject matter. The illustrated IMD 2862 provides neural stimulation signals for delivery to predetermined neural targets. The illustrated device includes controller circuitry 2863 and memory 2864. The controller circuitry is capable of being implemented using hardware, software, and combinations of hardware and software. For example, according to various embodiments, the controller circuitry includes a processor to perform instructions embedded in the memory to perform functions associated with the neural stimulation therapy. The illustrated device further includes a transceiver 2865 and associated circuitry for use to communicate with a programmer or another external or internal device. Various embodiments have wireless communication capabilities. For example, some transceiver embodiments use a telemetry coil to wirelessly communicate with a programmer or another external or internal device.

The illustrated device further includes neural stimulation output circuitry 2866 and sensor circuitry 2867. According to some embodiments, one or more leads are able to be connected to the sensor circuitry and neural stimulation circuitry. Some embodiments use wireless connections between the sensor(s) and sensor circuitry, and some embodiments use wireless connections between the stimulator circuitry and electrodes. According to various embodiments, the neural stimulation circuitry is used to apply electrical stimulation pulses to desired neural targets, such as through one or more stimulation electrodes 2868 positioned at predetermined location(s). Some embodiments use transducers to provide other types of energy, such as ultrasound, light or magnetic energy. In various embodiments, the sensor circuitry is used to detect physiological responses. Examples of physiological responses include cardiac activity such as heart rate, HRV, PR interval, T-wave velocity, and action potential duration. Other examples of physiological responses include hemodynamic responses such as blood pressure, and respiratory responses such as tidal volume and minute ventilation. The controller circuitry can control the therapy provided by system using a therapy schedule and a therapy titration routine in memory 2864, or can compare a target range (or ranges) of the sensed physiological response(s) stored in the memory 2864 to the sensed physiological response(s) to appropriately adjust the intensity of the neural stimulation/inhibition.

Some embodiments are adapted to change a stimulation signal feature, the neural stimulation target and/or change the neural stimulation vector as part of a neural stimulation titration routine. According to various embodiments using neural stimulation, the stimulation output circuitry 2866 is adapted to set or adjust any one or any combination of stimulation features based on commands from the controller 2863. Examples of stimulation features include the amplitude, frequency, polarity and wave morphology of the stimulation signal. Examples of wave morphology include a square wave, triangle wave, sinusoidal wave, and waves with desired harmonic components to mimic white noise such as is indicative of naturally-occurring baroreflex stimulation. Some embodiments are adapted to generate a stimulation signal with a predetermined amplitude, morphology, pulse width and polarity, and are further adapted to respond to a control signal from the controller to modify at least one of the amplitude, wave morphology, pulse width and polarity. Some embodiments are adapted to generate a stimulation signal with a predetermined frequency, and are further adapted to respond to a control signal from the controller to modify the frequency of the stimulation signal.

The controller 2863 can be programmed to control the neural stimulation delivered by the stimulation output circuitry 2866 according to stimulation instructions, such as a stimulation schedule, stored in the memory 2864. Neural stimulation can be delivered in a stimulation burst, which is a train of stimulation pulses at a predetermined frequency. Stimulation bursts can be characterized by burst durations and burst intervals. A burst duration is the length of time that a burst lasts. A burst interval can be identified by the time between the start of successive bursts. A programmed pattern of bursts can include any combination of burst durations and burst intervals. A simple burst pattern with one burst duration and burst interval can continue periodically for a programmed period or can follow a more complicated schedule. The programmed pattern of bursts can be more complicated, composed of multiple burst durations and burst interval sequences. The programmed pattern of bursts can be characterized by a duty cycle, which refers to a repeating cycle of neural stimulation ON for a fixed time and neural stimulation OFF for a fixed time.

According to some embodiments, the controller 2863 controls the neural stimulation generated by the stimulation circuitry by initiating each pulse of the stimulation signal. In some embodiments, the controller circuitry initiates a stimulation signal pulse train, where the stimulation signal responds to a command from the controller circuitry by generating a train of pulses at a predetermined frequency and burst duration. The predetermined frequency and burst duration of the pulse train can be programmable. The pattern of pulses in the pulse train can be a simple burst pattern with one burst duration and burst interval or can follow a more complicated burst pattern with multiple burst durations and burst intervals. In some embodiments, the controller 2863 controls the stimulator output circuitry 2866 to initiate a neural stimulation session and to terminate the neural stimulation session. The burst duration of the neural stimulation session under the control of the controller 2863 can be programmable. The controller may also terminate a neural stimulation session in response to an interrupt signal, such as may be generated by one or more sensed parameters or any other condition where it is determined to be desirable to stop neural stimulation.

The sensor circuitry is used to detect a physiological response. The detected response can be cardiac activity or surrogates of cardiac activity such as blood pressure and respiration measurements. Examples of cardiac activity include a P-wave and heart rate. The controller 2863 compares the response to a target range stored in memory, and controls the neural stimulation based on the comparison in an attempt to keep the response within the target range. The target range can be programmable.

The illustrated device includes a clock or timer 2869 which can be used to execute the programmable stimulation schedule. For example, a physician can program a daily schedule of therapy based on the time of day. The therapy can be delivered in synchrony with cardiac activity (synch routine in memory 2864) and with cardiac activity feedback (titrate/feedback routine in memory 2864). A stimulation session can begin at a first programmed time, and can end at a second programmed time. Various embodiments initiate and/or terminate a stimulation session based on a signal triggered by a user. Various embodiments use sensed data to enable and/or disable a stimulation session.

The illustrated memory includes a schedule. According to various embodiments, the schedule refers to the time intervals or period when the neural stimulation therapy is delivered. A schedule can be defined by a start time and an end time, or a start time and a duration. Various schedules deliver therapy periodically. According to various examples, a device can be programmed with a therapy schedule to deliver therapy from midnight to 2 AM every day, or to deliver therapy for one hour every six hours, or to delivery therapy for two hours per day, or according to a more complicated timetable. Various device embodiments apply the therapy according to the programmed schedule contingent on enabling conditions, such as poor glucose control, patient rest or sleep, low heart rate levels, and the like. The illustrated memory includes a synchronization routine and a titration feedback routine, which are used by the control to control the timing and adjustments of neural stimulation generated by the neural stimulator output circuitry.

FIG. 29 shows a system diagram of an embodiment of a microprocessor-based implantable device, according to various embodiments. The controller of the device is a microprocessor 2970 which communicates with a memory 2971 via a bidirectional data bus. The controller could be implemented by other types of logic circuitry (e.g., discrete components or programmable logic arrays) using a state machine type of design. As used herein, the term “circuitry” should be taken to refer to either discrete logic circuitry or to the programming of a microprocessor. Shown in the figure are three examples of sensing and pacing channels designated “A” through “C” comprising bipolar leads with ring electrodes 2972A-C and tip electrodes 2973A-C, sensing amplifiers 2974A-C, pulse generators 2975A-C, and channel interfaces 2976A-C. Each channel thus includes a pacing channel made up of the pulse generator connected to the electrode and a sensing channel made up of the sense amplifier connected to the electrode. The channel interfaces communicate bidirectionally with the microprocessor, and each interface may include analog-to-digital converters for digitizing sensing signal inputs from the sensing amplifiers and registers that can be written to by the microprocessor in order to output pacing pulses, change the pacing pulse amplitude, and adjust the gain and threshold values for the sensing amplifiers. The sensing circuitry of the pacemaker detects a chamber sense, either an atrial sense or ventricular sense, when an electrogram signal (i.e., a voltage sensed by an electrode representing cardiac electrical activity) generated by a particular channel exceeds a specified detection threshold. Pacing algorithms used in particular pacing modes employ such senses to trigger or inhibit pacing. The intrinsic atrial and/or ventricular rates can be measured by measuring the time intervals between atrial and ventricular senses, respectively, and used to detect atrial and ventricular tachyarrhythmias. The sensing of these channels can be used to detect cardiac activity for use in synchronizing neural stimulation and for use as feedback in titrating the neural stimulation.

The electrodes of each bipolar lead are connected via conductors within the lead to a switching network 2977 controlled by the microprocessor. The switching network is used to switch the electrodes to the input of a sense amplifier in order to detect intrinsic cardiac activity and to the output of a pulse generator in order to deliver a pacing pulse. The switching network also enables the device to sense or pace either in a bipolar mode using both the ring and tip electrodes of a lead or in a unipolar mode using only one of the electrodes of the lead with the device housing (can) 2978 or an electrode on another lead serving as a ground electrode. A shock pulse generator 2979 is also interfaced to the controller for delivering a defibrillation shock via a pair of shock electrodes 2980 and 2981 to the atria or ventricles upon detection of a shockable tachyarrhythmia.

Neural stimulation channels, identified as channels D and E, are incorporated into the device for delivering parasympathetic stimulation and/or sympathetic inhibition, where one channel includes a bipolar lead with a first electrode 2982D and a second electrode 2983D, a pulse generator 2984D, and a channel interface 2985D, and the other channel includes a bipolar lead with a first electrode 2982E and a second electrode 2983E, a pulse generator 2984E, and a channel interface 2985E. Other embodiments may use unipolar leads in which case the neural stimulation pulses are referenced to the can or another electrode. The pulse generator for each channel outputs a train of neural stimulation pulses which may be varied by the controller as to amplitude, frequency, duty-cycle, and the like. In this embodiment, each of the neural stimulation channels uses a lead which can be intravascularly disposed near an appropriate neural target. Other types of leads and/or electrodes may also be employed. A nerve cuff electrode may be used in place of an intravascularly disposed electrode to provide neural stimulation. In some embodiments, the leads of the neural stimulation electrodes are replaced by wireless links.

The figure illustrates a telemetry interface 2986 connected to the microprocessor, which can be used to communicate with an external device. The illustrated microprocessor is capable of performing neural stimulation therapy routines and myocardial (CRM) stimulation routines. The neural stimulation routines can target nerves to affect cardiac activity (e.g. heart rate and contractility). Examples of myocardial therapy routines include bradycardia pacing therapies, anti-tachycardia shock therapies such as cardioversion or defibrillation therapies, anti-tachycardia pacing therapies (ATP), and cardiac resynchronization therapies (CRT).

FIG. 30 is a block diagram illustrating an embodiment of an external system 3087. The external system includes a programmer, in some embodiments. In the illustrated embodiment, the external system includes a patient management system. As illustrated, the external system 3087 is a patient management system including an external device 3088, a telecommunication network 3089, and a remote device 3090. External device 3088 is placed within the vicinity of an IMD and includes external telemetry system 3091 to communicate with the IMD. Remote device(s) 3090 is in one or more remote locations and communicates with external device 3088 through network 3089, thus allowing a physician or other caregiver to monitor and treat a patient from a distant location and/or allowing access to various treatment resources from the one or more remote locations. The illustrated remote device includes a user interface 3092.

FIG. 31 illustrates a system embodiment in which an IMD 3193 is placed subcutaneously or submuscularly in a patient's chest with lead(s) 3194 positioned to stimulate a vagus nerve. According to various embodiments, neural stimulation lead(s) 3194 are subcutaneously tunneled to a neural target, and can have a nerve cuff electrode to stimulate the neural target. Some vagus nerve stimulation lead embodiments are intravascularly fed into a vessel proximate to the neural target, and use electrode(s) within the vessel to transvascularly stimulate the neural target. For example, some embodiments stimulate the vagus using electrode(s) positioned within the internal jugular vein. Other embodiments deliver neural stimulation to the neural target from within the trachea, the laryngeal branches of the internal jugular vein, and the subclavian vein. The neural targets can be stimulated using other energy waveforms, such as ultrasound and light energy waveforms. Other neural targets can be stimulated, such as cardiac nerves and cardiac fat pads. The illustrated system includes leadless ECG electrodes on the housing of the device. These ECG electrodes 3195 are capable of being used to detect heart rate, for example. Various embodiments include lead(s) positioned to provide a CRM therapy to a heart, and with lead(s) positioned to stimulate and/or inhibit neural traffic at a neural target, such as a vagus nerve, according to various embodiments.

FIG. 32 illustrates a system embodiment that includes an implantable medical device (IMD) 3296 with satellite electrode(s) 3297 positioned to stimulate at least one neural target. The satellite electrode(s) are connected to the IMD, which functions as the planet for the satellites, via a wireless link. Stimulation and communication can be performed through the wireless link. Examples of wireless links include RF links and ultrasound links. Examples of satellite electrodes include subcutaneous electrodes, nerve cuff electrodes and intravascular electrodes. Various embodiments include satellite neural stimulation transducers used to generate neural stimulation waveforms such as ultrasound and light waveforms. The illustrated system includes leadless ECG electrodes on the housing of the device. These ECG electrodes 3298 are capable of being used to detect heart rate, for example. Various embodiments include lead(s) positioned to provide a CRM therapy to a heart, and with satellite transducers positioned to stimulate/inhibit a neural target such as a vagus nerve, according to various embodiments.

One of ordinary skill in the art will understand that, the modules and other circuitry shown and described herein can be implemented using software, hardware, and combinations of software and hardware. As such, the term module is intended to encompass software implementations, hardware implementations, and software and hardware implementations.

The methods illustrated in this disclosure are not intended to be exclusive of other methods within the scope of the present subject matter. Those of ordinary skill in the art will understand, upon reading and comprehending this disclosure, other methods within the scope of the present subject matter. The above-identified embodiments, and portions of the illustrated embodiments, are not necessarily mutually exclusive. These embodiments, or portions thereof, can be combined. For example, various embodiments combine two or more of the illustrated processes. Two or more sensed parameters can be combined into a composite parameter used to provide a desired neural stimulation (NS) or anti-hypertension (AHT) therapy. In various embodiments, the methods provided above are implemented as a computer data signal embodied in a carrier wave or propagated signal, that represents a sequence of instructions which, when executed by a processor cause the processor to perform the respective method. In various embodiments, methods provided above are implemented as a set of instructions contained on a computer-accessible medium capable of directing a processor to perform the respective method. In various embodiments, the medium is a magnetic medium, an electronic medium, or an optical medium.

Although specific embodiments have been illustrated and described herein, it will be appreciated by those of ordinary skill in the art that any arrangement which is calculated to achieve the same purpose may be substituted for the specific embodiment shown. This application is intended to cover adaptations or variations of the present subject matter. It is to be understood that the above description is intended to be illustrative, and not restrictive. Combinations of the above embodiments as well as combinations of portions of the above embodiments in other embodiments will be apparent to those of skill in the art upon reviewing the above description. The scope of the present subject matter should be determined with reference to the appended claims, along with the full scope of equivalents to which such claims are entitled. 

What is claimed is:
 1. A baroreflex activation therapy (BAT) system, comprising: therapy circuitry connected to a first therapy terminal and a second therapy terminal and configured for producing a baroreflex activation therapy to provide a therapy to a patient through baroreflex modulation; measurement circuitry that is capable of measuring a voltage between a first measurement terminal and a second measurement terminal; and switching circuitry connected to the first measurement terminal, the second measurement terminal, the first therapy terminal, and the second therapy terminal; the switching circuitry being configured to couple a first electrode and a second electrode to the first therapy terminal and the second therapy terminal, respectively, for providing the baroreflex activation therapy to the body of a patient.
 2. The system of claim 1, wherein the switching circuitry is configured to couple the first electrode and a conductive housing of the BAT system to the first measurement terminal and the second measurement terminal, respectively, for measuring an electric potential difference within the body of the patient.
 3. The system of claim 2, wherein the conductive housing comprises a hermetically sealed housing defining an interior.
 4. The system of claim 3, wherein the therapy circuitry, the measurement circuitry, and the switching circuitry are all disposed in the interior of the housing.
 5. The system of claim 1, wherein the switching circuitry is configured to couple the first electrode and a third electrode to the first measurement terminal and the second measurement terminal, respectively, for measuring an electric potential difference within the body of the patient.
 6. The system of claim 1, further comprising: a memory storing a threshold value and disable circuitry configured to disconnect the therapy circuitry from at least one of the first and second electrodes if a measured value is below the threshold value.
 7. The system of claim 6, further comprising a pressure sensor.
 8. The system of claim 1, further comprising a controller operably connected to the therapy circuitry, the measurement circuitry and the switching circuitry, wherein the measurement circuitry includes a sensor connected to the controller.
 9. The system of claim 8, wherein the measurement circuitry is capable of measuring a biopotential within the body of the patient for producing an electrocardiogram signal; and the controller is configured for directing the switching circuitry to periodically connect one or more electrodes to the therapy circuitry for providing baroreflex activation therapy (BAT) to the body of the patient, and the controller is configured for directing the switching circuitry to periodically connect at least one of the first and second electrodes to the measurement circuitry for measuring the biopotential within the body of the patient for producing the electrocardiogram signal.
 10. The system of claim 8, wherein the sensor comprises a pressure sensor. 